US3926177A - Activity and respiration monitor - Google Patents

Activity and respiration monitor Download PDF

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Publication number
US3926177A
US3926177A US287844A US28784472A US3926177A US 3926177 A US3926177 A US 3926177A US 287844 A US287844 A US 287844A US 28784472 A US28784472 A US 28784472A US 3926177 A US3926177 A US 3926177A
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United States
Prior art keywords
pad
capacitance
activity
amplifier
output
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US287844A
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English (en)
Inventor
Jr Edward V Hardway
William H Holtman
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Cavitron Corp
Valleylab Inc
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Cavitron Corp
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Priority to US287844A priority Critical patent/US3926177A/en
Priority to CA179,964A priority patent/CA1007302A/en
Priority to GB4205273A priority patent/GB1439383A/en
Priority to IT52439/73A priority patent/IT996155B/it
Priority to DE19732345551 priority patent/DE2345551A1/de
Priority to NL7312419A priority patent/NL7312419A/xx
Priority to FR7332464A priority patent/FR2198722A1/fr
Priority to JP48101736A priority patent/JPS4965092A/ja
Priority to US05/597,726 priority patent/US4033332A/en
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Publication of US3926177A publication Critical patent/US3926177A/en
Priority to CA262,160A priority patent/CA1031829A/en
Assigned to COOPER LASERSONICS, INC. reassignment COOPER LASERSONICS, INC. ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: NORTIVAC, INC.
Assigned to CAVITRON, INC. reassignment CAVITRON, INC. ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: COOPER LASERSONICS, INC.
Assigned to VALLEYLAB, INC., A CORP. OF CO reassignment VALLEYLAB, INC., A CORP. OF CO MERGER (SEE DOCUMENT FOR DETAILS). 5/10/89 - DELAWARE Assignors: VALLEYLAB ULTRASONIC SURGICAL PORDUCTS, INC.
Assigned to VALLEYLAB ULTRASONIC SURGICAL PRODUCTS, INC. reassignment VALLEYLAB ULTRASONIC SURGICAL PRODUCTS, INC. CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). 2/03/89 - DELAWARE Assignors: V-CUSA, INC.
Assigned to V-CUSA, INC. reassignment V-CUSA, INC. CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). 12/30/88 - DELAWARE Assignors: CAVITRON, INC.
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6887—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient mounted on external non-worn devices, e.g. non-medical devices
    • A61B5/6892—Mats
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/1118—Determining activity level
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/113—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb occurring during breathing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A61B5/7242—Details of waveform analysis using integration

Definitions

  • a contactless act1v1ty and respiratlon monitor 1s described which includes a resilient, capacitive pad, U-S- 6 t may be a mattress or a pad used a ma[ [5 I tress having a apacitor therein responsive to the ac- Fleld of Search 2 2 tivity or respiration of a body lying on it.
  • 128/21 R 3,678,378 7/1972 Trott 61 a1 317/246 2 Clams 13 Drawmg Flgures 48 /49 /50 RAT E HII-LO RATE MEASURING RATE ALARM CIRCUIT -l COMP RATE Y 40 36 31 E3 41 42 DISPLA suMMms Lo w Low TIME AMP AC SYNC D.C.
  • This invention relates to a contactless monitor or alarm responsive to a condition of the bodies of humans or animals. In one of its aspects it relates to a monitor or alarm that responds to activity of humans or animals, and in another aspect it relates to a monitor or alarm for hospital and home use, which responds to respiration and apnea with particular application to detecting apnea in small infants.
  • Respiration monitors are used in hospitals to signal a nurse when a human patient develops an abnormal breathing rate or has stopped breathing. For example, it is common for the breathing of premature infants to be monitored in hospitals because a frequent cause of death is apnea (cessation of voluntary breathing), which can usually be corrected by cutaneous stimulation. Also, recent investigations have indicated that yearly in the United States, from 10,000 to 25,000 infants in their first few months who appear, even to physicians, to be normal and healthy, die in their cribs from unexplained causes. Most of these deaths occur at home during periods of sleep and are unobserved. The disease is often called the sudden infant death syndrome.
  • Some contactless monitoring devices are presently used in scientific research with non-human animals for studying the effects of various drugs, etc., on animal activity generally more rigorous than breathing.
  • the prior art has provided various devices using radio frequency or photo-electric signals to record activities which represent fairly large movements of the animal.
  • these devices are generally not sensitive enough to also respond selectively to very small movements such as breathing or to the cessation of breathing, particularly where the patient monitored is asmall infant.
  • the most commonly used prior apnea (and associated breathing) monitors are impedance plethysmographs requiring the patient to be wired with at least two electrodes installed on the chest.
  • Other similar devices are also provided which require the patient to be wired. These devices are all cumbersome and the electrodes coming loose is a troublesome problem. These devices are also obviously undesirable for use as a home monitor since the requirement for attaching wires to the baby and the dangers of strangulation would probably make it unattractive to most mothers.
  • One such device is a segmental air filled mattress in which very small volumes of air move from one inflated chamber in the mattress to another through a common manifold in response to movement of the mattress caused by breathing.
  • the manifold contains an electrical airflow sensor.
  • this device is cumbersome and capable of being deflated by a safety pin and is not suitable for home use. It is also subject to false alarms as its operation is dependent on the infants location on the mattress.
  • Another contactless monitor presently available has a small, thin transducer considerably smaller than the mattress of an incubator. The transducer is placed under the mattress to respond to motion caused by breathing of the baby.
  • this transducer must be placed directly under the baby and if the baby moves away from the transducer it is possible that the loss of signal will be so great that the device would not indicate apnea. To reduce this problem, it would be necessary to increase its sensitivity to such a value that it would be subject to failure to detect apnea from any slight movement of the incubator a failure that could cost the infant its life.
  • Another object of this invention is to provide such a monitor which detects and provides an alarm when apnea occurs for longer than a preselected period of time, or when respiratory rate falls either above or below a present level (or both).
  • Another object of this invention is to provide such a monitor in which a capacitive, non-pressurized incubator or crib mattress pad is used which has substantially equal levels of sensitivity to motion over the the entire upper surface.
  • Another object of this invention is to provide such a monitor which may be used to detect and provide an alarm when activity amplitudes of the body of the subject being monitored continues to exceed one or more given levels as would be the case if an infant were struggling for breath.
  • Another object of this invention is to provide such a monitor which may be used as an activity monitor which records or counts activity of a subject (particularly small animals) exceeding one or more given levels as events per unit time.
  • Another object of this invention is to provide a monitor such as described which may be suitable for home use for monitoring of small infants.
  • variable capacitance or capacitive pad substantially the same size as a mattress or other pad on which the subject to be monitored is lying (or the mattress or other pad may be the sensing pad) so that a given movement of the subject from breathing or other activity at substantially any place on the mattress or pad will cause a detectable and substantially equal change in the capacitance of the sensing pad.
  • An electronic capacitance sensing circuit is connected to the capacitive pad and responds to any change in capacitance to provide an electrical signal which may be used to detect activity or apnea and provide an alarm if a signal does not occur within a preselected period of time, i.e. lO-ZO seconds, or if any other abnormal condition occurs.
  • Circuits are provided which permit the apparatus to automatically respond to long term capacitance changes, for example the shift in weight of the subject, and to restore the baseline level to zero without appreciably affecting the sensitivity of the apparatus.
  • the circuits act as first order or single pole high pass (for example, breathing frequency) filters.
  • a fast zero switch may also be provided to shorten the response time of such circuits during very large capacitance changes.
  • FIG. 1 is a perspective view of the capacitive pad of this invention and shown with the alarm unit containing the electronic sensing circuits connected to it;
  • FIG. 2 is a top view in elevation of the capacitive pad of FIG. 1;
  • FIG. 3 is a cross section view taken at 3-3 in FIG. 2;
  • FIG. 4 is a schematic diagram of an equivalent circuit of the capacitive pad of FIG. 1 with a DC. drive shown to the pad and the input amplifier of the electronic sensing circuit shown;
  • FIG. 5 is a block diagram showing one form of DC. sensing circuitry that may be connected to the output of the amplifier in FIG. 4;
  • FIG. 6 is another equivalent circuit for the pad of FIG. 1 with an A.C. drive signal shown and the input amplifier for the electronic sensing circuitry shown;
  • FIG. 7 is a side view in elevation of another form of sensing pad of this invention, which is preferred.
  • FIG. 8 is a cross section taken at 8-8 in FIG. 6;
  • FIG. 9 is an equivalent circuit of the pad of FIG. 7 with an A.C. drive signal and with a basic block diagram of an electronic sensing circuit for the pad shown;
  • FIG. 10 is an overall block diagram of a respiration rate, activity, and apnea monitor using the principles of this invention.
  • FIG. 11 is a detailed schematic diagram of one form of. integrator and auto zero circuit that may be used withthe monitor of FIG. 10;
  • FIG. 12 is a detailed schematic of another form of a integrator and. auto zero circuit that may be used with themonitor of FIG. 10;
  • FIG. 13 is a detailed schematic diagram of one form of a fast zero switch circuit that may be used with the monitor of FIG. 10.
  • FIG. 1 shows infant 10 lying on a capacitive pad 11 which may be a mattress or mattress pad connected by shielded cabling 12 to an electronic alarm unit 13.
  • Alarm unit 13 which includes the electronic sensing circuitry of this invention, may include a digital readout 130 (which may also be an analog readout) of respiration rate, and a visual alarm 130 for indicating apnea or excessive activity.
  • An audio alarm (at the-rear of the case and not shown) sounds an audible alarm when apnea occurs for longer than a preset time interval.
  • capacitive pad 11 may be either a complete mattress, such as when a permanent installation in a hospital incubator is provided with the electrodes of this invention installed in it, or may just be a pad with the electrodes in it which can be placed under or on top of a regular mattress and is substantially the same size of the mattress, such as would be provided with a home monitor. Also, where animal activity is monitored it may be a pad in the bottom of the cage. Reference herein to pad or capacitive pad is intended to refer to both the integral capacitive mattress and the separate capacitive pad configuration.
  • FIGS. .2 and 3 One version of such a pad is shown in FIGS. .2 and 3.
  • the entire pad when using a DC. source to excite pad 11, the entire pad may be shielded from stray power line pickup by conductive plastic 14 connectedto the shield of cable 12.
  • pad 1 1 has two thin metal or fine conductive wire mesh electrodes 15 and 16, separated from each other by a layer 17 of resilient polyurethane foam or other elastomer foam, and from the top of pad 11 by a foam or other elastomer layer 18, and the bottom of pad 11 by a foam or other elastomer layer 19. It is preferable to have layer 19 denser than layers 17 and 18 for maximum sensitivity.
  • electrodes 15 and 16 cover substantially the entire area of pad 1 1 and form capacitive plates.
  • electrode 16 is connected to a source 20 of low level DC.
  • voltage E and a charge amplifier 21 having a feedback capacitance C,, a feedback resistor R, and a gain of K is connected at its input through cable 12 to electrode 15.
  • the input of amplifier 21 functions as a null junction N.
  • the output of amplifier 21 is labeled as a voltage E and will be responsive to the change in capacitance between electrodes 15 and 16 as the breathing of the baby causes movement of one of the electrodes with respect to the other.
  • W lowest angular breathing frequency assumed to be 2.1 radians per second for a breathing rate of 20 breaths per minute or 0.333 breaths per second.
  • This signal is sufficiently large to easily distinguish it from noise and use it in subsequent amplification.
  • FIG. is a block diagram showing how the output E of charge amplifier 21 would be used in a general purpose respiration monitor.
  • the output of amplifier 21 which serves as its own high pass filter with a cut-off frequency f is fed into low pass filter 22, which may cut off typically at 2 cps.
  • the filter output goes to a very high gain chopper stabilized amplifier 23 which may have a gain ranging from to 10
  • the amplifier 23 output goes to a high level comparator 24 and a low level comparator 25.
  • Comparator 24 senses large motions, i.e., greater than those caused by respiration indicating activity.
  • comparator 24 Single activity or prolonged activity signals from comparator 24 actuates an activity alarm 26, which may be a visual indication or an audio alarm.
  • the low level comparator 25 senses respiration and produces at least one pulse for each act of respiration. Comparator 25 output goes to a rate measuring circuit 27 which pro- 6 Jerusalem a current or voltage substantially proportional to rate which actuates a meter or display 28 (Le. an analog equivalent to digital display 13a in monitor 13).
  • comparator 25 also is connected to a time delay reset 29 which has a preset selectable time delay of, for example, between 10 and 20 seconds. Failure of a pulse to appear from comparator 25 within the preset time delay period causes the reset 29 to actuate an apnea alarm 30, which again may be an audio or visual alarm, or both.
  • rate circuit 27 may be connected to high or low rate alarms, and the output of the high limit comparator 24 may be recorded or counted to determine frequency of activity over long periods.
  • FIGS. 2-5 using a DC. drive voltage E while similar in some respects to the AC. embodiment of this invention to be described, are less preferred because of the require ment for complete shielding of the outer surface of the capacitive pad and the internal circuits from electrostatic pickup at power line frequency. Also, it would respond to electrostatic charges generated by motion of the cabling to the pad unless special non-microphonic cabling were used.
  • FIGS. 2-5 embodiment will provide an understanding of the principles of this invention as they are applicable to the construction of pad 11, and to the utilization of the output signals obtained from the pad.
  • FIG. 6 an A.C. version of the monitor of this invention is shown in which the driven electrode 16 of pad 11 is connected to one side of the secondary of a drive transformer 31, and receptor electrode 15 is connected to an AC. charge amplifier 32.
  • Transformer 31 provides drive voltages E and E,, of the same amplitude but opposite phase.
  • External fixed capacitors 33 and 34 are connected to the other side of the secondary of transformer 31 to balance out the gross static capacitance between electrodes 15 and 16.
  • the output E of amplifier 32 may be connected for utilization to circuitry such as shown in FIGS. l0-13 and to be described.
  • FIGS. 7 and 8 an alternate and in some applications of this invention a preferred form of pad 11 is shown which also may be used with an AC. capacitance sensing circuitry such as shown in FIGS. 9 and 10-13.
  • pad 11 is again divided into three layers of foamed material, with a top layer 18, bottom layer 19, and intermediate layer 17, and includes a receptor electrode 15 between layers 17 and 19, a first driven electrode between layers 18 and 17, and a second driven electrode 16b below layer 19 and between that layer and a conductive or non-conductive plastic cover 14a which encloses pad 11A.
  • a conductive cover may be used for shielding although this is not necessary in this embodiment if adaquate high pass filtering is used.
  • Electrodes 15, 16a and 16b preferably flexible wire mesh having substantially the same length and width as pad 11. However, if desired, the electrodes may be made of a conductive plastic sheeting or a multiplicity of thin metal plates connected by fine wires so that each 'plate moves independently.
  • the electrodes be sufficiently flexible and resilient to move with small movements of the pad over a large centrally located area of substantially all of the top surface area of the pad.
  • Foam layer 19 is preferably more dense and stiffer than foam layers 17 and 18.
  • FIG. 9 shows the basic block diagram of the front end of the A.C. sensing circuitry utilized with pad 1 1 shown schematically.
  • Driven electrodes 16a and 16b are connected to opposite sides of the secondary of a drive transformer 31 providing A.C. drive voltages E and -E of the same amplitude, but opposite phase, typically -25 volts at SOKHz, and driven by an oscillator 35.
  • the SOKHZ drive signals serve as a carrier signal.
  • Receptor electrode is connected to the input of a charge amplifier 32 of gain K which provides an output signal E proportional to capacitance changes between the electrodes 15 and 16a, and 15 and 16b, which, when equal, will be cancelled out.
  • the definitions of capacitance are essentially the same as used in Equation (1) above except that they are differential quantities (indicated by a prime).
  • C is the static capacitive imbalance which could be close to zero.
  • the output E of the charge amplifier 32 is given by:
  • Output signal E is coupled through a resistor R to an A.C. amplifier 36 which is connected to a synchronous demodulator 37 to provide a DC. output signal E Output signal E is coupled through a resistor R, to an integrator circuit 38 which has an integrating capacitor C, and integrates voltage E to produce a voltage E which is the input voltage to an auto-zero circuit 39.
  • Auto zero circuit 39 produces an A.C. output voltage E synchronized with oscillator 35 and opposite in phase to E, which is conducted through a resistor R to the input of A.C. amplifier 36.
  • Output voltage E may also be coupled to output and utilization circuitry such as provided in the monitor of FIG. 10.
  • Auto zero 39 functions as a synchronous modulator generating the signal voltage E to cancel long term changes in capacitance between electrodes 15, 16a and 16b, and allow only short term changes to appear as output voltage E How this works will become evident from the equations below where R R and K the ratio of the voltage levels (E E )/E K is the ratio of the angular voltage levels E and E, W is the frequency of the occurrence of signal E which, with a sleeping infant would generally be W the angular frequency of respiration of the baby; and T is the time constant of integrator 38 equal to R,C,:
  • the auto zero range must be sufficient to cancel any static imbalance, i.e.,
  • circuit components 36, 37, 38, and 39 provide the function of high level signal amplication and detection while functioning as an electronic high pass filter for rejecting the relatively long term capacitance changes.
  • both the DC. and A.C. versions include at least one single pole high pass electronic filter to reject or balance out static or long term changes of capacitance thousands of times larger than the changes that must be detected.
  • both the DC. and A.C. versions include at least one single pole high pass electronic filter to reject or balance out static or long term changes of capacitance thousands of times larger than the changes that must be detected.
  • the A.C. approach be used because:
  • the drive signal for example at 50 KHz, is non hazardous at reasonable voltage levels.
  • A.C. amplifier 36 (which may be several in series) are always operated within their range at balance, because of the auto-zero 39.
  • noise frequencies out of the breathing range can also be attenuated or substantially rejected.
  • Typical numbers used in apparatusused to date and employing the basic configuration of the figure of cir- 9 cuitry of FIG. 9 are:
  • the effective time constant of the auto-zero loop (i.e. the time required for a correction to be 63% completed) is:
  • FIGS. 10-13 a preferred form of activity and apnea monitor 13A similar to monitor 13 is shown, except that the respiration rate display is shown as an analog readout instead of the digital readout shown by the number 50 in a window 13a in FIG. 1. Also, an optional activity event counter is provided which is not shown in monitor 13 of FIG. 1.
  • pad 11, shown schematically, may be any of the embodiments described, but the embodiment of FIGS. 7 and 8 is illustrated in conjunction with the circuitry of FIG. 10.
  • the monitor of FIGS. 10-13 thus would be suitable for detecting and indicating apnea, rate of breathing and activity, and providing an alarm in the event of apnea and excessive activity, of human and non-human animals in the home, hospitals, or scientific laboratories.
  • drive transformer 31 is connected through isolation transformers T, and T, which are preferably provided for 50 Hz isolation and patient safety.
  • the output E, of charge amplifier 32 is fed to a summing amplifier and limiter 40 which functions as did resistors R, and R, in FIG. 9 to sum the outputs E, of charge amplifier 32 and E of auto-zero circuit 39, and to also keep relatively large and long term capacitance offsets created by patient body movements on the pad from saturating the circuitry and rendering the monitor inoperative.
  • the limiter section of amplifier 40 keeps A.C. amplifier 36 from completely saturating, allowing auto-zero circuit 39 to operate faster and keep the A.C.
  • summing amplifier and limiter 40 is conducted to the input of high gain A.C. amplifier 36 where it is amplified to usable level and then conducted to the input of synchronous demodulator 37
  • Synchro nous demodulator 37 which is synchronized with drive signals E and E,, as shown, detects only signals in proper phase and rejects noise, and provides a DC. output E which is then conducted to a low pass filter 41 which filters out the noise that was not rejected by synchronous demodulator 37.
  • Output E of synchronous demodulator 37 is also fed to integrator 38 and auto-zero circuit 39, which as noted, corrects for long term capacitance changes at the input to charge amplifier 32 by feeding back an A.C. signal equal in amplitude and opposite in phase as the signal created by the long term capacitance change at the output of amplifier 32.
  • This feedback signal is summed with the input signal at summing amplifier 40 which returns the DC output of synchronous demodulator 37 to zero at a slow rate, to provide a new baseline.
  • the DC. signal at the output of low pass filter 41 is conducted to a DC amplifier 42 where it is amplified for signal processing.
  • the output of DC. amplifier 42 is then fed to a high level comparator 43 and a low level comparator 44, both of which may be ordinary voltage level comparators which provide an output when the input voltage level exceeds a present threshold level.
  • a very low frequency high pass filter (not shown) may be used following the DC. amplifier to eliminate any problem with DC. offset due to bias currents.
  • High level comparator 43 may be set to respond to signal levels that are 10 times greater than the breathing signal, and which may be classified as signals representative of activity (other than breathing) of the subject being monitored.
  • the output of high level comparator 43 which is a low level (i.e.
  • the threshold of low level comparator 44 is set to detect smaller changes of capacitance at the input of charge amplifier 32 than comparator 43, and to classify these events as breaths.
  • the output of the low level comparator 44 is conducted to a breathing rate measuring circuit 48 and a time delay reset circuit 51 which resets a preselected time delay with each output signal from the low level comparator 44. Should the time delay not be reset for a preselected time ranging from 10-20 seconds, the time delay reset circuit 51 output changes state and is conducted to an apnea alarm 52.
  • the apnea alarm 52 can be a flashing light or an audible signal or both, each indicating that cessation of breathing has occurred.
  • the breathing rate measuring circuit 48 which measures the breathing rate and feeds a DC.
  • This DC. signal is also fed to a highlow breathing rate comparator 49 which gives an output if the breathing rate goes above or below a preset rate.
  • the output from the breathing rate comparator 49 is then conducted to a rate alarm 50 which can be a flashing light (such as light 13c in FIG. 1) or an audible 1 1 alarm.
  • a rate alarm 50 can be a flashing light (such as light 13c in FIG. 1) or an audible 1 1 alarm.
  • light alarm 130 may be used for both the breathing rate alarm and activity alarm 46.
  • the integrator circuit 38 and the auto-zero circuit 39 function as previously described and may take a number of different forms to provide a mechanical or electronic cancelling of long term capacitance changes.
  • Preferred circuits for auto-Zero 39 and integrator 38 are shown in FIG. 11 and less preferred circuits are shown in FIG. 12.
  • fast zero switch 45 may be a mechanical or electrical switch that functions as described. and a preferred form of such a switch is shown in FIG. 13. 7
  • an amplifier A is connected as a pure integrator having a feedback .capacitor with a capacitance of C and functions as the error amplifier for the auto-zerocircuit.
  • the DC. output E of synchronous demodulator 37 is conducted to the input of amplifier A which has zero volts or ground for its reference, through series resistors R and R
  • the integration time constant of amplifier A is determined by the product of input resistors (R R X C
  • Amplifier A is a summing amplifier and level shifter which provides one-half of a differential drive to the gate electrodes of two field effect transistors Q and Q As the output of amplifier A goes more positive, the output of amplifier A goes more negative.
  • the differential output voltages provided by amplifiers A and A are conducted to the gate electrodes of FETS Q and Q which function as variable impedance devices.
  • the inputs to FETS Q and Q are connected to drive trans former 31 and thus areSO KI-Iz sinewaves that are equal in amplitude, but opposite in phase.
  • the outputs of FETS Q and Q are connected together and summed at the input of an amplifier A and then amplified by amplifier A to provide feedback voltage E
  • the gain of A ;and thus the signal level of the feedback voltage, E is determined by a feedback resistor R, connected from its output to its input, and the impedance of FETS Q and Q which varies as a function of the DC. voltage levels at their gate electrodes.
  • the output E of amplifier A will change amplitude .and phase as the differential DC. voltage applied to the gate electrodes of FETS Q and Q goes from one extreme to the other.
  • the output E of A is fed back to the input of summing amplifier 40 and summed with the output E of the charge amplifier to cancel this signal out and maintain the baseline (E at zero volts, D.C.
  • FIG. 12 Another version of an auto-zero circuit 39 is shown in FIG. 12. This circuit is the same as shown in FIG. 11 except that it uses varactor diodes D and D as the variable elements in the feedback loop. The capacitance from anode to cathode of the varactors changes as the DC. bias voltage across the diode is varied. Amplifier A again is connected as a pure integrator and functions as the error amplifier for the auto-zero circuit. The DC. output E of synchronous demodulator 37 is fed to the input of amplifier A which is again referenced to Zero volts, through series input resistors R and R The integration time constant is again determined by the product of (R R X C,.
  • Amplifier A is a summing amplifier and level shifter which provides one-half of the differential DC. bias voltage to D and D D and D are driven with 50 KHz sinewaves from drive transformer 31 that are equal in amplitude and opposite in phase. The output of D and D is summed at the input of charge amplifier A and its output is then amplified to a usable level E and fed to the capacitance measuring circuit at the input of amplifier 40 in FIG. 10 where it is summed with the output E of the input charge amplifier. Asthe input voltage E to A goes above or below zero volts, the DC. bias voltage across D and D varies to provide the necessary amplitude and phase to correct for the change in capacitance at the input of the capacitance measuring circuit, in the same manner as described with respect to the FIG. 11 embodiment.
  • fast zero circuit 45 is illustrated as a mechanical switch shunting input resistor R to reduce the integration time constant of integrator 38 whenever voltage E exceeds a preset high level.
  • a preferred form of this switch includes transistors Q and Q, and afield effect transistor Q that exhibits a very high impedance when turned off and a low impedance when turned on.
  • the output of high level comparator 43 which forexample may be at a 5 volts positive, is conducted to transistor Q Transistors Q and Q, are normally conducting keeping the gate of the FET Q at about negative 15 volts which keeps it turned off.
  • the input amplifier is shown as a charge amplifier i.e. with a capacitor in the feedback loop clamping the receptor electrode of the pad at virtual ground.
  • the chargeamplifier with the DC. feedback resistor R serves as a high pass filter. In the AC.
  • circuits R has no function except to stabilize the input amplifier, but the charge amplifier with capacitor C provides power amplification of the high frequency signal with minimal phase shift and makesthe three-terminal capacitive measurement substantially, independent of cable length.
  • any suitable input amplifier may be used if all other functional circuit requirements are met in the alternate circuit.
  • this invention is concerned with a resilient mattress or pad withat least'one flexible electrode extending over a-substantial portion (i.e. the part that the baby is likely to be over) of the mattress surface area, so that a capacitance change occurswhen the mattress surface is 13 depressed.
  • Essential to operation of the invention is a high pass electronic filter with time constant R C in FIG. 4 and in the AC. version and wherein the time constant is long enough to allow passage of signals occurring at the breathing or activity frequencies being detected.
  • an auto-zero circuit is used (which may be any suitable working embodiment of a synchronous modulator or analog multiplier which instantaneously multiplies the 50 KHZ signal by the integrator output) to provide a long term balancing signal E the latter being the product of one phase of the reference 50 KHZ carrier voltage and the integrator output voltage E.
  • the product E R is used to cancel long term changes at the output of the amplifier 32, and, of course, cancellation could also be effected at the input of amplifier 32.
  • pad 11 and monitor 13 can provide surveillance of a subject, such as an infant, without any need for wiring the subject, and with complete safety to the subject.
  • the monitor would be equally suitable for use in a hospital, home or a scientific or medical laboratory. Either cessation of respiration, (apnea) or struggling activity such as would occur when an infant is attempting to regain its breath, would initiate an alarm and provide an opportunity for corrective measures to be taken.
  • Apparatus responsive to movement of the body of a human or animal to provide an indication of a condition of such a body comprising, in combination:
  • a resilient, capacitive pad adapted to respond to movement of such a body when disposed over the pad to provide a capacitance change, said pad including at least two electrodes extending beneath a substantial portion of the upper surface area of said pad, and a dielectric between said electrodes;
  • capacitance sensing means means for connecting said driving signal means and said sensing means to said electrodes; said sensing means being responsive to said capacitance change to provide an output signal representing said indication, said sensing means comprising an electronic high pass filter for substantially rejecting changes in capacitance of said pad of relatively long term as compared to the term of capacitance changes caused by the condition being indicated, and means for shortening the response time of said high pass filter when such activity exceeds a predetermined level.
  • the apparatus of claim 1 further including a first level detector responsive to capacitance changes caused by breathing of said body, and a second level detector responsive to capacitance changes caused by larger activity than breathing of said body.

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  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
US287844A 1972-09-11 1972-09-11 Activity and respiration monitor Expired - Lifetime US3926177A (en)

Priority Applications (10)

Application Number Priority Date Filing Date Title
US287844A US3926177A (en) 1972-09-11 1972-09-11 Activity and respiration monitor
CA179,964A CA1007302A (en) 1972-09-11 1973-08-30 Activity and respiration monitor
GB4205273A GB1439383A (en) 1972-09-11 1973-09-06 Activity and respiration monitor
IT52439/73A IT996155B (it) 1972-09-11 1973-09-10 Perfezionamento nei monitor di attivita motoria e di respirazione
DE19732345551 DE2345551A1 (de) 1972-09-11 1973-09-10 Aktivitaets- und atmungs-monitor
NL7312419A NL7312419A (sv) 1972-09-11 1973-09-10
FR7332464A FR2198722A1 (sv) 1972-09-11 1973-09-10
JP48101736A JPS4965092A (sv) 1972-09-11 1973-09-11
US05/597,726 US4033332A (en) 1972-09-11 1975-07-21 Activity and respiration monitor
CA262,160A CA1031829A (en) 1972-09-11 1976-09-28 Activity and respiration monitor

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US287844A US3926177A (en) 1972-09-11 1972-09-11 Activity and respiration monitor

Related Child Applications (1)

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US05/597,726 Division US4033332A (en) 1972-09-11 1975-07-21 Activity and respiration monitor

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US3926177A true US3926177A (en) 1975-12-16

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US287844A Expired - Lifetime US3926177A (en) 1972-09-11 1972-09-11 Activity and respiration monitor

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US (1) US3926177A (sv)
JP (1) JPS4965092A (sv)
CA (1) CA1007302A (sv)
DE (1) DE2345551A1 (sv)
FR (1) FR2198722A1 (sv)
GB (1) GB1439383A (sv)
IT (1) IT996155B (sv)
NL (1) NL7312419A (sv)

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US4403215A (en) * 1977-12-27 1983-09-06 Hellige, Gmbh Apparatus for automatically monitoring body functions
DE3009216A1 (de) * 1979-03-13 1980-09-25 Instrumentarium Oy Geraet zur anzeige und/oder aufzeichnung der bewegungen einer person zu medizinischen untersuchungszwecken
US4320766A (en) * 1979-03-13 1982-03-23 Instrumentarium Oy Apparatus in medicine for the monitoring and or recording of the body movements of a person on a bed, for instance of a patient
USRE32180E (en) * 1980-02-12 1986-06-10 Composite sheets constituting electromechanical transducers and transducers equipped with such sheets
WO1982002823A1 (en) * 1981-02-27 1982-09-02 David William Douglas Method and apparatus for detecting apnea
US4381788A (en) * 1981-02-27 1983-05-03 Douglas David W Method and apparatus for detecting apnea
US4444199A (en) * 1981-07-21 1984-04-24 William A. Shafer Method and apparatus for monitoring physiological characteristics of a subject
US4809702A (en) * 1981-11-20 1989-03-07 Universite De Franche-Comte Method for recording foetal movements during pregnancy and apparatus for carrying out the said method
EP0091522A3 (en) * 1982-04-14 1984-11-14 The Hospital For Sick Children Respiration monitor
EP0091522A2 (en) * 1982-04-14 1983-10-19 The Hospital For Sick Children Respiration monitor
WO1986000996A1 (en) * 1984-07-18 1986-02-13 Rudiger Benkendorf Movement detection apparatus
US4971065A (en) * 1985-02-11 1990-11-20 Pearce Stephen D Transducer for detecting apnea
US4895160A (en) * 1985-05-23 1990-01-23 Heinrich Reents Apparatus for measuring the life functions of a human being, particularly an infant
US4827763A (en) * 1986-04-11 1989-05-09 Purdue Research Foundation Pressure mapping system with capacitive measuring pad
US5010772A (en) * 1986-04-11 1991-04-30 Purdue Research Foundation Pressure mapping system with capacitive measuring pad
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US4838279A (en) * 1987-05-12 1989-06-13 Fore Don C Respiration monitor
US7141021B2 (en) 1987-06-26 2006-11-28 Resmed Limited Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient
US7004908B2 (en) 1987-06-26 2006-02-28 Resmed Limited Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient
US6635021B1 (en) * 1987-06-26 2003-10-21 Resmed Limited Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient
FR2651988A1 (fr) * 1989-09-19 1991-03-22 Martin Thierry Dispositif de surveillance des mouvements spontanes d'un etre vivant.
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US5144284A (en) * 1991-05-22 1992-09-01 Hammett Rawlings H Patient-monitoring bed covering device
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US5659395A (en) * 1992-06-23 1997-08-19 Footmark, Inc. Method and apparatus for analyzing feet
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US5361133A (en) * 1992-06-23 1994-11-01 Footmark, Inc. Method and apparatus for analyzing feet
US8152732B2 (en) 1992-08-19 2012-04-10 Lynn Lawrence A Microprocessor system for the analysis of physiologic and financial datasets
US5295490A (en) * 1993-01-21 1994-03-22 Dodakian Wayne S Self-contained apnea monitor
WO1999042967A1 (en) * 1995-03-02 1999-08-26 Individual Monitoring Systems, Inc. Methods and apparatus for monitoring activity and providing feedback
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IT996155B (it) 1975-12-10
FR2198722A1 (sv) 1974-04-05

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